US5051239A - Flow device for use in hemorrhaging time measuring apparatus and method of measuring a hemorrhaging - Google Patents
Flow device for use in hemorrhaging time measuring apparatus and method of measuring a hemorrhaging Download PDFInfo
- Publication number
- US5051239A US5051239A US07/272,944 US27294488A US5051239A US 5051239 A US5051239 A US 5051239A US 27294488 A US27294488 A US 27294488A US 5051239 A US5051239 A US 5051239A
- Authority
- US
- United States
- Prior art keywords
- aperture
- set forth
- suction tube
- housing
- blood
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
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Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/483—Physical analysis of biological material
- G01N33/487—Physical analysis of biological material of liquid biological material
- G01N33/49—Blood
- G01N33/4905—Determining clotting time of blood
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
- G01N33/86—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving blood coagulating time or factors, or their receptors
Definitions
- the apparatus for measuring hemorrhaging time in vitro uses a through-flow device having a separating wall in the form of a porous member with an aperture therein.
- the porous member is supported on a support structure which is not permeable to air, and is of such a design configuration that blood passes only through the aperture therein, and cannot flow round the sides of the porous member. That provides an apparatus, and therewith a method, for measuring hemorrhaging time in vitro, in which it is possible to simulate the hemorrhaging processes under in-vivo conditions.
- An object of the invention is to provide a flow device for use in a hemorrhaging time measuring apparatus, which can not only accurately simulate in-vivo conditions but which also provides for a high level of reproducibility of the measurement results.
- Another object of the present invention is to provide a flow device for use in a hemorrhaging time measuring apparatus, which is of a simple construction and reliable in operation while affording the option of a wide range of operating procedures.
- Still another object of the present invention is to provide a method of measuring blood hemorrhaging time under simulated in-vivo conditions with a high degree of measurement result reproducibility.
- Yet a further object of the present invention is to provide a blood hemorrhaging time measuring method which can be carried out in a simple and rational manner with a wide range of operating materials.
- a flow device for use in a hemorrhaging time measuring apparatus, wherein the flow device comprises a housing through which the blood to be tested flows, passing through at least one aperture within the housing.
- a receiving means is disposed downstream of the aperture, for receiving the blood which has flowed therethrough and a suction tube is arranged upstream of the aperture.
- the suction tube projects into a cavity in the housing, which is disposed upstream of the aperture and which air-tightly surrounds the aperture, with the downstream end of the suction tube being disposed in the vicinity of the aperture.
- the downstream end of the suction tube is disposed at such a spacing from the aperture that, with a given suction effect, thrombus formation occurs in the aperture.
- a method of measuring blood hemorrhaging time in particular in the first phase of thrombocyte aggregation, provides that the blood to be tested is sucked under a given suction force through the suction tube of the above-defined flow device, and the amount of blood which flows through the suction tube is measured. Thrombus formation is produced at the aperture in the device.
- the construction of the flow device and the method in accordance with the principles of the present invention ensure that thrombus formation takes place at a precisely defined location in the device, that is to say at the aperture which is provided in the housing, for example in a wall portion of the housing or in a separating or partitioning wall which defines the cavity in the housing, into which the suction tube projects.
- the aperture which is provided in the housing for example in a wall portion of the housing or in a separating or partitioning wall which defines the cavity in the housing, into which the suction tube projects.
- the range of variation attained in the measurement results has been found to be below 5%, thus satisfying the requirements generally made in respect of clinical and scientific uses.
- the at least one aperture is provided in a partitioning or separating wall which is of a pressure-tight nature and which is pressure-tightly connected to the housing on the interior thereof, to define the cavity into which the suction tube projects.
- the separating wall may be in the form of a porous member, with a pore size of less than 5 ⁇ m and larger than 0.01 ⁇ m, with an aperture therein.
- the diameter of the aperture may be between about 50 and 300 ⁇ m, preferably between 150 and 250 ⁇ m.
- the porous member may be permeated and/or coated with for example collagen.
- the separating wall is also possible for the separating wall to be made from a non-porous material, for example a plastic plate member, which is coated with collagen in particular in the region of the aperture therethrough. It is also possible for the separating wall to be made from a plastic foil which is suitably supported in the housing by a support disc or other support structure. The plastic disc may also be in the form of a portion of artificial skin, as is known for example as a skin implant from U.S. Pat. No. 4,458,678. It is further possible to use a separating wall consisting of a plastic plate or a plastic foil comprising a polymerised compound on an acrylic acid base, as is disclosed for example in U.S. Pat. No.
- a suitable material for the separating wall member is also cellulose acetate which is coated with collagen.
- collagen it would also be possible to use another agent which induces thrombocyte aggregation, for example adenosine diphosphate, or a thrombocyte-activating agent, for example PAF which is a phospholipid (see Rompps Chemie-Lexikon, 8th edition, pages 3159 and 3160), such materials being used to provide a coating on the separating wall at least in the region of the aperture therethough.
- the diameter of the aperture may be from about 20 ⁇ m to 500 ⁇ m, like also the inside diameter of the suction tube.
- the inside diameter of the suction tube is preferably from about 150 to 250 ⁇ m.
- agents which influence the hemorrhaging processes also makes it possible to obtain certain diagnostic indications or indications in respect of pharmacological influences on the blood, for example thrombocyte adhesion or aggregation, as for example by pain-killing agents, sleeping drugs or the like.
- agents may involve for example a coagulation-inhibiting agent such as heparin, Na-citrate and coumarin derivatives, or thrombocyte aggregation-inhibiting agents such as for example acetyl salicylic acid, sulfinpyrazone or ticlopidin, or a thrombocyte aggregation-inducing agent such as for example adenosine diphosphate, PAF, collagen or ristocetin.
- a coagulation-inhibiting agent such as heparin, Na-citrate and coumarin derivatives
- thrombocyte aggregation-inhibiting agents such as for example acetyl salicylic acid, sulfinpyrazone or ticlopidin
- a thrombocyte aggregation-inducing agent such as for example adenosine diphosphate, PAF, collagen or ristocetin.
- v.Willebrand syndrome in the following fashion. That syndrome is to be attributed to a reduced level of adhesion capability of the blood platelets, so that a retarded drop in the amount of blood flowing through the device can be found in the measurement operation. If in a subsequent measuring run ristocetin is added to the blood, it is found that that retarded drop in the flow of blood, which results from the thrombus formation phenomenon, no longer occurs.
- the apparatus may be put to a further use for example in relation to rheological blood investigations (hemorrheology) or in determining the viscosity of blood.
- the respective amounts of blood flowing through the device may be measured while maintaining a constant suction pressure acting thereon at different points of time.
- a device which does not have the above-mentioned partitioning or separating wall with the aperture therethrough that is to say a device in which a storage vessel in which the blood to be tested is contained is connected to the receiving vessel by way of the suction tube, wherein the required suction force for sucking the blood through the device is produced for example by way of an opening in the receiving container, or the above-mentioned varying pressures or pulsating pressures are applied to the suction tube by way of the opening in the receiving container.
- FIG. 1 is a diagammatic view of an embodiment of a flow device according to the present invention
- FIG. 2 is a cut-away view of part of the FIG. 1 device
- FIG. 3 shows a further embodiment of the flow device according to the invention.
- FIG. 4 is a view on an enlarged scale of the area around the aperture in the flow device of a third embodiment of the present invention.
- a flow device 1 as illustrated therein in accordance with the principles of the present invention, comprises housingportions 17 and 9 having configurations thereon such that the housing portions 17 and 9 can be fitted together in the illustrated position, as will be described below.
- the housing portion 17 is substantially in the form of a receiving container for receiving blood which has flowed throughthe device 1, being of a volume which approximately corresponds to the volume that the blood to be tested occupies in a supply container as indicated at 10 in FIG. 1.
- a wall portion in the form as illustrated of a separating wall 2, which has an aperture 4 therein.
- the separating wall 2 may be of a porous nature, as described in above-mentioned German specification No.
- the separating wall 2 which is of a pressure-tight nature and which is pressure-tightly fitted at its peripheral edge to the wall of the housing portion 17 lies on the bottom part 12 of the housing portion 17.
- the separating wall 2 may additionally be supported by a support structure (not shown) which is arranged above the separating wall and which bears against the top surface of the separating wall 2.
- the bottom 12 of the housing portion 17 has an opening 11 therethrough, which surrounds the aperture 4 in the separating wall 2. As stated above, the separating wall 2 lies in a pressure-tight condition on the bottom 12 of the housing portion 17.
- the opening 11 in the bottom 12 of the housing portion 17 of the flow device 1 is surrounded by an inner wall 7 which is the inner wall of a tube portion 13 formed on the bottom 12 on the outside thereof, that is to say extending downwardly from the bottom 12 in the position of the device as shown in FIG. 1.
- the tube portion 13 is fitted into a receiving bore of suitable configuration in the housing portion 9, as can be clearly seen from FIG. 1.
- the outside diameter of the tube portion 13 is matched to theinside diameter of the receiving bore in the housing portion 9, thus providing a snug press fit between the two components.
- the flow device 1 further includes a suction tube 3 through which the bloodto be tested and investigated is sucked from the supply container 10.
- the tube 3 is fixedly inserted into a through bore in the housing portion 9 and projects into the space defined in the housing portion 17 of the device 1, which is surrounded by the inside wall 7 of the tube portion 13. In that arrangement there is a space 5 between the wall 7 and the peripheral surface 6 of the suction tube 3.
- the provision of the space 5 ensures that the upper part of the suction tube 3 can be loosely introduced into the space defined by the tube portion 13.
- the spacing of the peripheral surface 6 of the suction tube 3 from the wall 7 which extends at least substantially parallel thereto may be up to 1.0 mm,more particularly 0.5 mm.
- the spacing b ensures that the suction tube 3 can be satisfactorily fitted into the tube portion 13, taking account of tolerances which may occur.
- the spacing b may also be such that in the measuring operation, no blood can pass into the space 5 between the wall 7of the tube portion 13 and the peripheral surface 6 of the suction tube 3.
- the inside diameter of the suction tube 3, as indicated at d in FIG. 2, maybe from about 20 to 500 ⁇ m, preferably from 150 to 250 ⁇ m.
- the suction tube 3 may comprise any suitable material, preferably polytetrafluoroethylene.
- the suction tube 3 is so arranged and positioned that the downstream end 8 thereof is disposed in the vicinity of the aperture 4 through the separating wall 2.
- the spacing of the end 8 of the suction tube 3 from theunderneath edge of the aperture 4, as indicated at a in FIG. 2, is from 0.1to 6.0 mm.
- the outside diameter of the suction tube 3, as indicated at e inFIG. 2 is such as to ensure adequate mechanical stability, and may be from0.05 to 1.5 mm, preferably 1.0 mm.
- the inside diameter of the space enclosed by the wall 7, as indicated at f in FIG. 2 also depends on the outside diameter e of the suction tube 3, for the above-indicated reasons,and in the illustrated embodiment may be from 1.5 to 2.5 mm, preferably 2.0mm.
- the blood is sucked out of the container 10 through the suction tube 3 by means of a suction and measuring device 14.
- a suitable reduced pressure is produced in the interior of the housing portion 17 which is communicated with the suction and measuring device 14 by way of an opening 15 in the upper wall part of the housing portion 17, and a suction tube 16 which connects the housing portion 17 tothe device 14.
- That reduced pressure is also to be found upstream of the aperture 4 in the space which is enclosed by the wall 7 and into which thesuction tube 3 extends.
- That reduced pressure also occurs in the through-flow bore or capillary passage in the suction tube 3. That is ensured by virtue of the fact that the tube portion 13 which pressure-tightly surrounds the aperture 4 at the underside of the separating wall 2 is also pressure-tightly fitted into the corresponding bore or recess accommodating same in the lower housing portion 9.
- the suction and measuring device 14 operates in such a way that in the measurement operation, a constant suction force or pressure is maintained by way of the suction tube 16, as far as the through bore of the suction tube 3, whereby the constant suction pressure is applied to the blood which is to be drawn up into the suction tube 3 from the container 10.
- Thesuction and measuring device may be of any suitable construction, being forexample of the kind disclosed in above-mentioned German laid-open application (DE-OS) No 35 41 057.
- the blood gradually forms a plug in the region of the aperture 4, in particular in the area around the aperture atthe underside of the separating wall 2 and extending into the aperture 4, by virtue of aggregation of the thrombocytes. That plug finally entirely closes off the aperture 4.
- Blood which flows away laterally towards the wall 7 is deposited in the region formed by the spacing a of the end 8 of the suction tube 3 from the underneath surface of the separating wall 2. It has been found that, when the dimensions of the structure are suitably selected, the device ensures that no blood penetrates between the peripheral surface 6 of the suction tube 3 and the oppositely disposed part of the wall 7. It has also been found that thrombus formation always occurs in a reproducible fashion at the aperture 4. That therefore affordsa high level of reproducibility of the measurement results and thus provides accurate information about the hemorrhaging process, in particular concerning thrombocyte aggregation in the first phase.
- FIG. 3 That device is generally similar to the device shown in FIGS. 1 and 2 and it will therefore not be described in detail again at this stage, for that reason. It will be seen from FIG. 3 however that the space 5 around the aperture 4 in the separating wall 2,being the space into which the upper end 8 of the suction tube 3 projects, is enlarged relative to the remainder of the space defined between the suction tube 3 and the wall structure surrounding it, in the region of theend 8 of the suction tube.
- the wall portion which forms the separating wall 2 may be formed in one piece with the housing portion 17.
- Such a construction may be for example of the configuration shown in FIG. 4.
- the aperture 4 is formed directly in the bottom part of the housing portion 17.
- the space 5 which surrounds the aperture 4and which is enclosed by the wall 7 is also formed in or at the bottom of the housing portion 17.
- the upper end 8 of the suction tube 3 extends into the space 5 formed in the bottom of the housing portion 17, in the manner shown in FIG. 4.
- At least the region which is disposed around the aperture 4 and which is towards the end 8 of the suction tube 3 is provided with a coating or layer as indicated at 18 which is formed from a thrombocyte aggregation-inducing agent or a thrombocyte-activating factor, as referred to hereinbefore.
- a flushing agent such as for example a NaCl-solution or albumen is deposited in the region between the end 8 of the suction tube and the aperture 4, laterally of the aperture 4, without passing into the space between the wall 7 and the peripheral surface 6 of the suction tube 3.
- the blood which then follows on flows through the aperture 4 and adhesion of the thrombocytes causes thrombocytes to adhere in the region of the aperture 4, with the result that a thrombus is formed, resulting in the aperture 4 being closed.
- the aperture 4 may also be omitted so that the tube 3 is directly connected to the receiving space defined by the housing portion 17.
- the separating wall material may comprise extra-cellular matrix which itself has thrombocyte aggregation-inducing properties or which is additionally provided with a thrombocyte aggregation-inducing agent.
- the material of the separating wall may also consist of a shaped body of collagen material. Animal skin is also suitable as a material for the separating wall.
- the agents which influence the hemorrhaging procedures may also be added to the blood to be tested, by way of the material of the separating wall 2.
- the substance or substances involved which is or are selected in dependence on a given diagnosis to be carried out in the measurement operation, may also be incorporated into the material of the separating wall, which for that purpose is in particular of a porous nature. The substance or substances is or are then added to the blood from the material of the separating wall during the measuring operation.
Abstract
Description
Claims (21)
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE3739247A DE3739247C2 (en) | 1987-11-19 | 1987-11-19 | Bleeding time measuring device |
DE3739247 | 1987-11-19 | ||
EP88117388.4 | 1988-10-19 |
Publications (1)
Publication Number | Publication Date |
---|---|
US5051239A true US5051239A (en) | 1991-09-24 |
Family
ID=6340813
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US07/272,944 Expired - Lifetime US5051239A (en) | 1987-11-19 | 1988-11-18 | Flow device for use in hemorrhaging time measuring apparatus and method of measuring a hemorrhaging |
Country Status (5)
Country | Link |
---|---|
US (1) | US5051239A (en) |
EP (1) | EP0316599B1 (en) |
JP (1) | JP2686790B2 (en) |
DE (1) | DE3739247C2 (en) |
ES (1) | ES2056089T3 (en) |
Cited By (40)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5296379A (en) * | 1990-03-23 | 1994-03-22 | Peter Gorog | Apparatus and method for modeling arterial thrombus formations |
US5339830A (en) * | 1992-01-21 | 1994-08-23 | Blake Joseph W Iii | Blood coagulation test system |
US5352413A (en) * | 1991-05-28 | 1994-10-04 | Baxter Diagnostics Inc. | Device for the safe removal of blood from a supply vessel |
US5460779A (en) * | 1991-05-28 | 1995-10-24 | Dade International Inc. | Device for the automatic examination of blood samples |
WO1996000898A1 (en) * | 1994-06-30 | 1996-01-11 | Dade International Inc. | Combination reagent holding and test device |
US5599718A (en) * | 1991-12-19 | 1997-02-04 | Gorog; Diana | Measurement of the thrombolytic activity of blood |
US5854076A (en) * | 1994-06-30 | 1998-12-29 | Dade International Inc. | Method for testing coagulation of blood through bioactive porous partition members |
US5854423A (en) * | 1996-03-20 | 1998-12-29 | Venegas; Jose G. | Apparatus and method for assessment of visco-elasticity and shear adherence strength properties of blood clots |
US5888826A (en) * | 1994-06-30 | 1999-03-30 | Dade Behring Inc. | Combination reagent holding and test device |
US5916813A (en) * | 1996-12-20 | 1999-06-29 | Xylum Corporation | Thrombotic and/or thrombolytic status analyser |
US5919419A (en) * | 1994-02-22 | 1999-07-06 | Orion-yhtyma Oy | Analyzer cuvette, method and diagnostic test kit for determination of analytes in whole blood samples |
US5958716A (en) * | 1996-06-06 | 1999-09-28 | Dade Behring Inc. | Blood factor assay |
US6077233A (en) * | 1998-03-12 | 2000-06-20 | Blake, Iii; Joseph W | Blood coagulation test system |
US6156530A (en) * | 1994-11-08 | 2000-12-05 | Global Hemostasis Institute Mgr Ab | Method for analysis of haemostatic activity |
US6159741A (en) * | 1996-04-30 | 2000-12-12 | Dr. Michael Kratzer Gmbh | Process for measuring blood platelet aggregation or blood coagulation |
US20020029621A1 (en) * | 2000-05-26 | 2002-03-14 | Symyx Technologies, Inc. | Instrument for high throughput measurement of material physical properties and method of using same |
US6393898B1 (en) * | 2000-05-25 | 2002-05-28 | Symyx Technologies, Inc. | High throughput viscometer and method of using same |
US20030041676A1 (en) * | 2001-08-24 | 2003-03-06 | Symyx Technologies, Inc. | High throuhput mechanical property testing of materials libraries using a piezoelectric |
US20030055587A1 (en) * | 2001-09-17 | 2003-03-20 | Symyx Technologies, Inc. | Rapid throughput surface topographical analysis |
US20030141613A1 (en) * | 2002-01-31 | 2003-07-31 | Symyx Technologies, Inc. | High throughput preparation and analysis of plastically shaped material samples |
US20030203500A1 (en) * | 2002-04-26 | 2003-10-30 | Symyx Technologies, Inc. | High throughput testing of fluid samples using an electric field |
US6690179B2 (en) | 2001-08-24 | 2004-02-10 | Symyx Technologies, Inc. | High throughput mechanical property testing of materials libraries using capacitance |
US20040077091A1 (en) * | 2002-10-18 | 2004-04-22 | Symyx Technologies, Inc. | High throughput permeability testing of materials libraries |
US6736017B2 (en) | 2001-08-24 | 2004-05-18 | Symyx Technologies, Inc. | High throughput mechanical rapid serial property testing of materials libraries |
US6769292B2 (en) | 2001-08-24 | 2004-08-03 | Symyx Technologies, Inc | High throughput rheological testing of materials |
US6772642B2 (en) | 2001-08-24 | 2004-08-10 | Damian A. Hajduk | High throughput mechanical property and bulge testing of materials libraries |
US20040177707A1 (en) * | 2001-08-24 | 2004-09-16 | Symyx Technologies, Inc. | High throughput mechanical rapid serial property testing of materials libraries |
US6857309B2 (en) | 2001-08-24 | 2005-02-22 | Symyx Technologies, Inc. | High throughput mechanical rapid serial property testing of materials libraries |
US6860148B2 (en) | 2001-08-24 | 2005-03-01 | Symyx Technologies, Inc. | High throughput fabric handle screening |
US20050136541A1 (en) * | 2003-12-23 | 2005-06-23 | Dade Behring Marburg Gmbh | Cartridge for monitoring the function of a device for testing blood platelet function, method for function monitoring, and use of a test fluid |
US20060269978A1 (en) * | 2005-04-25 | 2006-11-30 | Haworth William S | Method and device for monitoring platelet function |
US20070212744A1 (en) * | 2004-04-21 | 2007-09-13 | Michael Kratzer | Device For Analyzing The Coagulation Or Aggregation Behavior Of Blood |
US20070254325A1 (en) * | 2006-04-28 | 2007-11-01 | Dade Behring Marburg Gmbh | Method and device for the determination of platelet function under flow conditions |
US20070254324A1 (en) * | 2006-04-28 | 2007-11-01 | Dade Behring Marburg Gmbh | Method for determination of platelet function under flow conditions |
US7309607B2 (en) | 2002-09-10 | 2007-12-18 | Placor Inc. | Method and device for monitoring platelet function |
US7399637B2 (en) | 2004-04-19 | 2008-07-15 | Medtronic, Inc. | Blood coagulation test cartridge, system, and method |
US7422905B2 (en) | 2004-02-27 | 2008-09-09 | Medtronic, Inc. | Blood coagulation test cartridge, system, and method |
US7439069B2 (en) | 2004-02-27 | 2008-10-21 | Nippoldt Douglas D | Blood coagulation test cartridge, system, and method |
US20100099130A1 (en) * | 2006-10-25 | 2010-04-22 | Placor Inc. | Methods and devices for monitoring platelet function |
JP2012194181A (en) * | 2011-03-15 | 2012-10-11 | Siemens Healthcare Diagnostics Products Gmbh | Devices and methods for determining platelet function |
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DE4244931C2 (en) * | 1991-05-28 | 1998-07-30 | Dade Int Inc | Automatic blood sample examination appts. |
DE4209872C2 (en) * | 1991-05-28 | 1996-11-14 | Dade Int Inc | Device for measuring the bleeding time in vitro |
DE4244975C2 (en) * | 1991-05-28 | 1999-07-29 | Dade Int Inc | Automatic blood sample examination appts. |
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1987
- 1987-11-19 DE DE3739247A patent/DE3739247C2/en not_active Expired - Lifetime
-
1988
- 1988-10-19 EP EP88117388A patent/EP0316599B1/en not_active Expired - Lifetime
- 1988-10-19 ES ES88117388T patent/ES2056089T3/en not_active Expired - Lifetime
- 1988-11-18 US US07/272,944 patent/US5051239A/en not_active Expired - Lifetime
- 1988-11-19 JP JP63293454A patent/JP2686790B2/en not_active Expired - Lifetime
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US3900290A (en) * | 1973-03-13 | 1975-08-19 | Int Octrooi Mij Octropa Nl1973 | Method and apparatus for determining the degree of platelet aggregation in blood |
US4604894A (en) * | 1982-12-23 | 1986-08-12 | Michael Kratzer | System for measuring bleeding time in vitro |
US4780418A (en) * | 1985-11-19 | 1988-10-25 | Michael Kratzer | Method and apparatus for measuring the aggregation of blood platelets or the coagulation of blood |
Cited By (63)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5296379A (en) * | 1990-03-23 | 1994-03-22 | Peter Gorog | Apparatus and method for modeling arterial thrombus formations |
US5744098A (en) * | 1991-05-28 | 1998-04-28 | Dade International Inc. | Device for the automatic examination of blood samples |
US5352413A (en) * | 1991-05-28 | 1994-10-04 | Baxter Diagnostics Inc. | Device for the safe removal of blood from a supply vessel |
US5460779A (en) * | 1991-05-28 | 1995-10-24 | Dade International Inc. | Device for the automatic examination of blood samples |
US5599718A (en) * | 1991-12-19 | 1997-02-04 | Gorog; Diana | Measurement of the thrombolytic activity of blood |
US5339830A (en) * | 1992-01-21 | 1994-08-23 | Blake Joseph W Iii | Blood coagulation test system |
US5919419A (en) * | 1994-02-22 | 1999-07-06 | Orion-yhtyma Oy | Analyzer cuvette, method and diagnostic test kit for determination of analytes in whole blood samples |
US5888826A (en) * | 1994-06-30 | 1999-03-30 | Dade Behring Inc. | Combination reagent holding and test device |
WO1996000898A1 (en) * | 1994-06-30 | 1996-01-11 | Dade International Inc. | Combination reagent holding and test device |
US6702987B1 (en) * | 1994-06-30 | 2004-03-09 | Dade Behring Inc. | Bioactive porous partition members |
US5602037A (en) * | 1994-06-30 | 1997-02-11 | Dade International, Inc. | Combination reagent holding and test device |
US5854076A (en) * | 1994-06-30 | 1998-12-29 | Dade International Inc. | Method for testing coagulation of blood through bioactive porous partition members |
US6156530A (en) * | 1994-11-08 | 2000-12-05 | Global Hemostasis Institute Mgr Ab | Method for analysis of haemostatic activity |
US5854423A (en) * | 1996-03-20 | 1998-12-29 | Venegas; Jose G. | Apparatus and method for assessment of visco-elasticity and shear adherence strength properties of blood clots |
US6159741A (en) * | 1996-04-30 | 2000-12-12 | Dr. Michael Kratzer Gmbh | Process for measuring blood platelet aggregation or blood coagulation |
US5958716A (en) * | 1996-06-06 | 1999-09-28 | Dade Behring Inc. | Blood factor assay |
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Also Published As
Publication number | Publication date |
---|---|
DE3739247A1 (en) | 1989-06-01 |
EP0316599A3 (en) | 1990-10-10 |
DE3739247C2 (en) | 1996-11-21 |
JPH01201157A (en) | 1989-08-14 |
EP0316599A2 (en) | 1989-05-24 |
EP0316599B1 (en) | 1994-05-04 |
JP2686790B2 (en) | 1997-12-08 |
ES2056089T3 (en) | 1994-10-01 |
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